EP1223428B1 - Procédé de mesure du volume de globules rouges individuels - Google Patents

Procédé de mesure du volume de globules rouges individuels Download PDF

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Publication number
EP1223428B1
EP1223428B1 EP01129401A EP01129401A EP1223428B1 EP 1223428 B1 EP1223428 B1 EP 1223428B1 EP 01129401 A EP01129401 A EP 01129401A EP 01129401 A EP01129401 A EP 01129401A EP 1223428 B1 EP1223428 B1 EP 1223428B1
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EP
European Patent Office
Prior art keywords
area
suspension
red blood
intensity
measuring
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Expired - Lifetime
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EP01129401A
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German (de)
English (en)
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EP1223428A1 (fr
Inventor
Klaus W. Berndt
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Becton Dickinson and Co
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Becton Dickinson and Co
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
    • G01N15/10—Investigating individual particles
    • G01N15/14—Optical investigation techniques, e.g. flow cytometry
    • G01N15/1468—Optical investigation techniques, e.g. flow cytometry with spatial resolution of the texture or inner structure of the particle
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
    • G01N15/01—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials specially adapted for biological cells, e.g. blood cells
    • G01N2015/012—Red blood cells
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
    • G01N15/10—Investigating individual particles
    • G01N2015/1006—Investigating individual particles for cytology

Definitions

  • the present invention relates to the field of quantitative microspectroscopy, and in particular to a method for measuring the volume of individual red blood cells.
  • MCV Mean Cell Volume
  • RW Red Cell Distribution Width
  • Impedance counters are complex and expensive instruments that require very careful adjustment and control of instrument and sample parameters.
  • a major disadvantage of flow cytometers is the fact that the parameters of light scattering depend not only on cell volume, but also on the cell's shape.
  • Gray, Hoffman and Hansen proposed a new optical method for determining the volume of cells in a flow cytometer (M.L. Gray, R.A. Hoffman, W.P. Hansen, "A new method for cell volume measurement based on volume exclusion of a fluorescent dye", Cytometry 3 (1983), 428 - 432).
  • the cells are suspended in a fluorescent dye, which is unable to penetrate the cell membrane.
  • the level of fluorescence which is produced when a narrow stream of the cell suspension is excited by a focused laser beam, will remain constant until a cell arrives in the illuminated region thereby causing a decrease in fluorescence intensity, which is directly proportional to the volume of the cell.
  • the available data acquisition time can be significantly increased by suspending the cells in a stationary sample and applying digital imaging fluorescence microscopy (see P.L. Becker, F.S. Fay, "Cell-volume measurement using the digital imaging fluorescence microscope", Biophysical Journal 49 (1986), A465).
  • digital fluorescence microscopy approach a calibration procedure is required in order to determine the cell volume. Recktenwald and co-workers have introduced a method where the calibration is performed by means of optical transparent and non-fluorescent microspheres that are suspended together with the cells (D. Recktenwald, J. Phi-Wilson, B. Verwer, "Fluorescence quantitation using digital microscopy", Journal Physical Chemistry 97 (1993), 2868 - 2870).
  • the volume of individual spheres is determined by measuring their projection area under the microscope and transforming this number into a volume, assuming an ideal spherical shape.
  • the decrease in fluorescence intensity as a result of the spheres' volume that is being excluded from emitting fluorescence is used as the required calibration parameter.
  • the advantage of this approach is given by the fact that the calibrating particles are located within the sample itself. In other words, a calibration is performed on the very same sample container, and no extra calibration sample is required.
  • the use of calibration spheres within a cell suspension is not without problems.
  • the introduction of the spheres represents an additional step in the workflow. In systems that are designed for high throughput, this additional step would represent a disadvantage.
  • Recktenwald and co-workers observed a tendency of the fluorescent dye molecules to settle down on the sphere's surface, which causes an error.
  • the use of microspheres can represent a problem, if, for example, a thin sample thickness in the order of a few micrometers or less is needed.
  • EP 1 150 114 A1 discloses a method for determining the volume of particles that are suspended in a liquid sample.
  • a liquid sample that contains suspended particles is deposited into an optical cuvette having an entrance window and an output window at a known distance from each other.
  • a light absorbing dye that does not leak into the suspended particles is mixed into the liquid sample.
  • Light is sent through the cuvette of such a wavelength that it is highly absorbed by the added dye, but only weakly by the suspended particles.
  • the cuvette is placed in front of an imaging photo detector and light intensities are measured.
  • one measurement is performed of light travelling through the liquid sample between the entrance window and the output window.
  • Another measurement is performed of light travelling through an area of the cuvette having a different distance between the two cuvette windows.
  • a different, e.g. reduced distance can be achieved by gluing a small flat piece of glass having a known thickness onto one of the cuvette windows.
  • the above objective is achieved by depositing a liquid sample that contains suspended red blood cells into an optical cuvette having an input window and an output window, by adding and evenly distributing an absorbing dye into the liquid that does not leak into the red blood cells, and that is able to absorb light at wavelengths that are only weakly absorbed by the red blood cells, by illuminating the sample through the input window at a wavelength that is absorbed by said dye, but only weakly absorbed by the red blood cells, by measuring the transmitted light intensity reemerging through the output window in an area that contains no red blood cells, by changing the cuvette thickness in that area by a well-defined amount and measuring the reemerging light intensity in the same area again, by measuring the reemerging light intensity in an area where a red blood cell resides, by measuring the reemerging light intensity in an area close to that same red blood cell, and by calculating the volume of the red blood cell based on these light intensity values and the known change in cuvette thickness.
  • FIG. 1 depicts a measuring set-up with an optical cuvette having a stiff input window and a flexible output window, and containing a liquid sample comprising suspended red blood cells.
  • FIG. 2 illustrates a complete set-up comprising sample container, XYZ-stage, transmission microscope, CCD camera, and computer.
  • FIG. 3 shows schematically an optical cuvette with a region containing a weakly absorbing red blood cell, and another region containing no cells.
  • the arrows illustrate the stream of photons traversing the sample, whereby the decrease in width is meant as an indication of the decreasing light intensity as a result of absorption.
  • FIG. 4 illustrates the calibration procedure, where the cuvette thickness in an area that contains no red blood cells is changed by a well-defined amount, h, and the reemerging light intensities, I 1 and I 2 , are measured prior to and after changing the thickness.
  • the cuvette thickness has been reduced.
  • FIG. 5 illustrates the measuring procedure, where the reemerging light intensities, I 4 and I 3 , are measured in an area where a red blood cell resides, and in an area close to that same cell.
  • I 4 and I 3 reemerging light intensities
  • FIG. 6 shows a calculated plot of reemerging light intensity in arbitrary units, if a cuvette thickness of approximately 18 ⁇ m is increased in ten steps of 0.2 ⁇ m each, up to approximately 20 ⁇ m.
  • a liquid sample that contains suspended red blood cells is deposited into an optical cuvette having an input window and an output window.
  • the cuvette is relatively thin and suitable to be positioned onto the sample stage of a transmission microscope.
  • the cuvette can be built by placing a flexible #1 coverslip of 24 mm x 50 mm size onto spacers that are residing on a common microscope slide of 25 mm x 75 mm size.
  • the preferred height of the spacers is approximately 200 ⁇ m.
  • An optical cuvette is any container that is able to hold a liquid sample within its interior space and that has a transparent entrance window and a transparent exit window, usually on opposite sides, allowing for transmission measurement. It would also be possible to use a container with one transparent window on one side and a mirror on the other side. In this case, light would enter the container through said one transparent window, would cross the liquid sample twice, and would exit the container through the same window. The one window would function as both entrance window and exit window.
  • the invention is not limited to containers for microscopic analysis, but is applicable also for containers of larger size that are interrogated on optical systems other than microscopes.
  • An absorbing dye is added to, and evenly distributed within the liquid sample.
  • the dye is selected so that it does not leak into the red blood cells. Also, it should absorb excitation light within a spectral region where the absorption within the red blood cells is only weak. Since hemoglobin is the dominant absorber in red blood cells, the illumination wavelength has to be longer than 600 nm.
  • One good candidate dye is TO-PRO-3 (sold, for example, by Molecular Probes, Inc., Eugene, Oregon), that can be illuminated within a wavelength range around to 640 nm, where it has an absorption coefficient of 1.14*10 5 L/Mcm.
  • Another possible dye would be TO-PRO-5 (sold by Molecular Probes, Inc.), which also does not penetrate into the red blood cells, can be illuminated around 750 nm, and has an absorption coefficient of 1.21 * 10 5 L/Mcm.
  • the invention is not limited to the two dyes mentioned above. Many other dyes are available that fulfill the spectral conditions for measurements on red blood cells, and even more dyes are available that fulfill the spectral conditions for other particles. It would of course also still be within the spirit of the present invention to add and evenly distribute the absorbing dye within the liquid sample prior to disposing the sample into the container.
  • FIG. 1 depicts a measuring set-up with an optical cuvette (20) having a stiff input window (1), a flexible output window (3) and containing a liquid sample (4) comprising suspended red blood cells.
  • the cuvette is built by using a common microscope slide (1) that carries spacers (2, 2') to hold a flexible cover slip (3).
  • the suspension of red blood cells in a liquid such as blood plasma (4) is contained between slide (1) and cover slip (3).
  • the optical cuvette is positioned on an XYZ-stage (5) of a common transmission microscope (7) having interchangeable objective lenses (8, 9, and 10) and a sample illumination source (6).
  • microscope (7) is equipped with a CCD camera (21) that is connected to a computer (22) for storing data and performing image-processing procedures.
  • Computer (22) is also connected to XYZ-stage (5) to move cuvette (20) as needed.
  • FIG. 3 shows schematically an optical cuvette with a region containing a weakly absorbing red blood cell, and another region containing no cells.
  • the arrows illustrate the stream of photons traversing the sample, whereby the decrease in width is meant as an indication of the decreasing light intensity as a result of absorption.
  • the optical absorption within a red blood cell is so weak that no decrease in intensity occurs.
  • cuvette (20) is moved upwards by means of stage (5) until flexible window (3) comes into physical contact with a fixed plunger (11) that is mounted onto objective lens (10) in such a way that the focal plane of microscope (7) lies within liquid sample (4) if flexible window (3) is touching plunger (11).
  • cuvette (20) is being moved in X- and Y-directions until a sample area containing no red blood cells comes into the field of view. If the sample is whole blood, then it is appropriate to use a cuvette thickness in the range of 2 ⁇ m to 30 ⁇ m in order to have areas containing no red blood cells readily available. For diluted blood samples, thicker cuvettes can be used.
  • the sample is illuminated with light of appropriate wavelength by means of illumination source (6), and the reemerging intensity of the transmitted light, I 1 , in that area is measured by means of CCD camera (21), and the result stored in computer (22). This is illustrated in FIG. 4.
  • cuvette (20) is moved further upwards by means of stage (5) by a small, but precisely known distance, h. Moving cuvette (20) upward against fixed plunger (11) results in a reduction in the optical path length within the cuvette by an amount identical to h.
  • a new reemerging light intensity, I 2 in the same area is measured, and the result stored in computer (22).
  • the new light intensity, I 2 has a higher value than the first intensity, I 1 , because a smaller sample thickness results in less absorption of light within the sample.
  • the two reemerging light intensity values, I 1 and I 2 , together with the change in optical path length, h, can be used to calibrate the set-up by calculating a ratio "change in reemerging light intensity/change in sample thickness". Referring to FIG. 4, this calibration can be explained as follows.
  • I 1 I 0 *10 -ac*h 1
  • I 0 the illumination intensity
  • a the absorption coefficient of the light-absorbing dye
  • c the concentration of the dye.
  • h 1 the optical path length (or thickness) of cuvette (20) at the area that is measured.
  • Equation (3) indicates that there is no need for knowing the absolute cuvette thickness, h 1 , or for measuring the illumination intensity, I 0 , because these two quantities are canceled out.
  • the volume of a single red blood cell is determined in the following way:
  • the reemerging light intensity, I 4 is measured in an area, A RBC , where a red blood cell resides.
  • a RBC area where a red blood cell resides.
  • the red blood cell has a cylindrical shape of area A RBC , and of height h RBC (see FIG. 5).
  • h 2 height of the liquid sample layer, h 2 , which has not to be equal to h 1
  • I' 0 illumination intensity
  • Equation (9) shows that the method according to the present invention is based on differential measurements regarding the thickness of the cuvette, and on ratiometric measurements regarding the reemerging light intensities. In other words, there is no need to know the absolute thickness of the cuvette. Moreover, there is no need to know the excitation intensity which is injected into the cuvette.
  • Equation (9) shows also that any long-term drift in the instrumental parameters is canceled out. This results from the fact that the volume of a red blood cell, V RBC , is calculated from a ratio of photocurrents. In other words, if the calibration procedure is executed closely in time with the measurement, then the method according to the present invention is very robust. This condition will always be fulfilled, since the calibration procedure is performed on the very same sample that is being measured.
  • the red blood cell has a cylindrical shape. It can be shown that the shape of the red blood cell can be irregular and that the Z - position of the cell within the cuvette has no impact on the calculated cell volume.
  • equation (10) the quantities and represent the independent X- and Y-variables within the red blood cell.
  • This aspect of the invention allows for the use of simple one-size one-shape integration areas for all individual cells that are studied. Consequently, the required calculations can be executed within a shorter time interval. It should be noted that it is assumed, as equation (11) implies, that the intensity I 3 near the cell is constant.
  • I 4 ( ⁇ , ⁇ ) is measured in practice as an intensity of single CCD pixels
  • I 3 can be determined with maximum precision as the sum of all pixel intensities over an area, divided by the number of pixels. In other words, I 3 is the average pixel intensity near the cell.
  • FIG. 6 shows a calculated plot of reemerging light intensity in arbitrary units, if a cuvette thickness of approximately 18 ⁇ m is increased in ten steps of 0.2 ⁇ m each, up to approximately 20 ⁇ m.
  • the light intensity as a function of thickness can be represented by a straight-line relationship.
  • the method for measuring the volume of individual red blood cells according to the present invention can be applied to whole blood or to diluted blood samples.
  • the present invention can also be applied to a whole cluster of red blood cells or other particles in a liquid suspension, and not only to individual particles or cells. It would also be possible to apply this method to other particles suspended in liquids such as beads or other particles or cells, for example, prokaryotic, bacterial, eukaryotic, mammalian, tissue culture or human cells.
  • the present invention can also be applied to particles or cells in other liquid suspensions or samples or dilutions thereof, such other medical or biological samples including tissue cultures or other cells in culture, including bacterial cultures, and other body fluids such as blood, urine, sputum, saliva and lymph fluid.
  • the method can also be applied in cuvettes of higher thickness.
  • a flexible window is only one example for achieving a change in the thickness of the cuvette. It would also be possible to use a stiff window, but spacers made out of a flexible material such as rubber. Still another embodiment would be possible by utilizing a flexible cuvette wall instead of localized spacers.
  • the change in cuvette thickness can be achieved by leaving the main part of the cuvette fixed, and acting with a positive or negative force onto the window, so that the window is moving. Such positive or negative forces may even involve the use of pressure or vacuum.
  • the invention is not limited to optical microscopes. Any imaging system that allows measuring transmitted light intensities in areas that contain a particle and in areas that do not contain a particle are suitable to practice the present invention.
  • the imaging system may contain lenses, but may also use fiber-optic elements in so-called proximity configurations. In this case, a coherent fiber-optic bundle is arranged between a cuvette window and an imaging photodetector.
  • the step of calibration i.e. determining the quantity "change in reemerging light intensity / change in sample thickness" according to equation (3) can also be performed in close proximity to the particle under investigation.
  • the thickness of the optical cuvette in this area is being changed by an amount ⁇ h, and new reemerging light intensity is measured.
  • the reemerging light intensity in the area occupied by the particle is measured. While the first two steps provide the required calibration, the second and the third step provide the two reemerging light intensity values that are needed for the actual volume measurement.
  • This second procedure according to the present invention has the advantage that three instead of four steps are required.
  • the first procedure according to the present invention allows performing the calibration within a cuvette area of increased thickness, which would allow for a more precise calibration value due to the increased reemerging light intensity levels.
  • the user has to decide, based on the priorities at hand

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  • Chemical & Material Sciences (AREA)
  • Dispersion Chemistry (AREA)
  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Analytical Chemistry (AREA)
  • Biochemistry (AREA)
  • General Health & Medical Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Immunology (AREA)
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  • Investigating Or Analysing Biological Materials (AREA)
  • Optical Measuring Cells (AREA)
  • Investigating Or Analysing Materials By Optical Means (AREA)

Claims (6)

  1. Procédé de mesure du volume de particules dans un liquide, le procédé comprenant :
    (a) l'obtention d'une suspension de particules dans un liquide ;
    (b) le dépôt de ladite suspension dans un récipient ayant au moins une fenêtre flexible ou montée de manière flexible, ledit récipient étant approprié pour effectuer des mesures de transmission ;
    (c) l'ajout d'un colorant absorbant à ladite suspension dans ledit récipient qui ne s'infiltre pas dans lesdites particules, dans lequel ledit colorant est capable d'absorber une lumière d'excitation à des longueurs d'ondes qui sont si faiblement absorbées par lesdites particules qu'aucune baisse d'intensité n'intervient ;
    (d) l'illumination de ladite suspension avec de la lumière, de sorte que la longueur d'onde de ladite lumière soit choisie de manière à ce que ladite lumière soit absorbée par ledit colorant, mais si faiblement absorbée par lesdites particules qu'aucune baisse d'intensité n'intervient ;
    (e) la mesure d'une première intensité (I1) de la lumière transmise qui réémerge de ladite suspension dans une première zone de ladite suspension, ladite première zone ne contenant aucune particule ou étant située proche d'une particule ;
    (f) le changement de l'épaisseur dudit récipient dans ladite première zone d'une quantité connue en appuyant sur ladite au moins fenêtre flexible ou montée de manière flexible depuis l'extérieur et la mesure d'une seconde intensité (I2) de la lumière transmise qui réémerge de ladite suspension dans ladite première zone ;
    (g) la mesure d'une troisième intensité (I4) de la lumière transmise qui réémerge de ladite suspension dans une seconde zone de ladite suspension, ladite seconde zone contenant au moins une particule ; et
    (h) la détermination du volume (VRBC) de ladite au moins une particule sur la base desdites valeurs de l'intensité de la lumière transmise et dudit changement connu d'épaisseur (Δh) dudit récipient.
  2. Procédé selon la revendication 1 comprenant de manière supplémentaire l'étape suivante entre les étapes (g) et (h) :
    mesure d'une quatrième intensité (I3) de la lumière transmise qui réémerge d'une troisième zone de ladite suspension proche de ladite au moins une particule dans ladite seconde zone.
  3. Procédé selon l'une quelconque des revendications 1 ou 2 dans lequel les étapes (b) et (c) sont effectuées dans l'ordre : étape (c) - étape (b).
  4. Procédé selon l'une quelconque des revendications 1 à 3 dans lequel la particule est une cellule humaine ou un globule rouge.
  5. Procédé selon l'une quelconque des revendications 1 à 3 dans lequel le liquide est un échantillon biologique ou médical qui comprend un liquide organique, des cellules d'une culture tissulaire ou des cellules bactériennes.
  6. Procédé selon l'une quelconque des revendications 1 à 3 dans lequel le récipient est une cuvette optique (20) et le colorant est choisi parmi le groupe constitué de TO-PRO-3 et TO-PRO-5.
EP01129401A 2001-01-03 2001-12-10 Procédé de mesure du volume de globules rouges individuels Expired - Lifetime EP1223428B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US753403 2001-01-03
US09/753,403 US6633369B2 (en) 2001-01-03 2001-01-03 Method for measuring the volume of individual red blood cells

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EP1223428A1 EP1223428A1 (fr) 2002-07-17
EP1223428B1 true EP1223428B1 (fr) 2005-12-07

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US (1) US6633369B2 (fr)
EP (1) EP1223428B1 (fr)
JP (1) JP2002323438A (fr)
AT (1) ATE312346T1 (fr)
DE (1) DE60115591T2 (fr)
MX (1) MXPA01013032A (fr)

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US20040090613A1 (en) * 2002-07-17 2004-05-13 Goix Philippe J. Method for measuring the volume of cells or particles
US6873725B2 (en) * 2002-09-09 2005-03-29 Coulter International Corp. Simultaneous measurement and display of 3-D size distributions of particulate materials in suspensions
US11181465B2 (en) 2018-02-01 2021-11-23 Toray Industries, Inc. Device for evaluating particles in liquid and method for operating same
WO2023007341A1 (fr) * 2021-07-26 2023-02-02 Agilent Technologies, Inc. Porte-échantillon amélioré

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Publication number Priority date Publication date Assignee Title
US4284355A (en) * 1979-10-29 1981-08-18 Ortho Diagnostics, Inc. Automated method for cell volume determination
EP0479231B1 (fr) * 1990-10-01 1996-03-27 Canon Kabushiki Kaisha Appareil et procédé pour la mesure d'un échantillon
US5563070A (en) * 1993-05-28 1996-10-08 Omron Corporation Method of counting reticulocytes
WO1996020456A1 (fr) * 1994-12-23 1996-07-04 International Remote Imaging Systems, Inc. Procede et appareil pour analyser des particules dans un echantillon liquide et les afficher
US6127184A (en) * 1998-03-07 2000-10-03 Robert A. Levine Calibration of a whole blood sample analyzer
US6235536B1 (en) * 1998-03-07 2001-05-22 Robert A. Levine Analysis of quiescent anticoagulated whole blood samples
US6350613B1 (en) * 1998-03-07 2002-02-26 Belton Dickinson & Co. Determination of white blood cell differential and reticulocyte counts
US5948686A (en) * 1998-03-07 1999-09-07 Robert A. Leuine Method for performing blood cell counts
US6359683B1 (en) * 2000-04-27 2002-03-19 Becton, Dickinson And Company Method for determining the volume of particles suspended in liquids

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MXPA01013032A (es) 2004-05-21
JP2002323438A (ja) 2002-11-08
US6633369B2 (en) 2003-10-14
US20020118354A1 (en) 2002-08-29
EP1223428A1 (fr) 2002-07-17
DE60115591D1 (de) 2006-01-12
DE60115591T2 (de) 2006-08-17
ATE312346T1 (de) 2005-12-15

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